CN108195900B - Electrochemical sensor with temperature compensated hematocrit test function - Google Patents
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Classifications
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume, or surface-area of porous materials
- G01N15/04—Investigating sedimentation of particle suspensions
- G01N15/05—Investigating sedimentation of particle suspensions in blood
Abstract
The invention belongs to the technical field of medical equipment, and relates to an electrochemical sensor with a temperature compensation function for testing the hematocrit. The electrochemical sensor comprises a substrate, an electrode layer, a reaction reagent, a pad layer and a hydrophilic film layer; a notch is arranged at the sample inlet end of the substrate; the electrode layer comprises a correction electrode system and a detection electrode system which are positioned on the same plane, the correction electrode system comprises a pair of correction electrodes, and the hematocrit test is carried out by applying alternating current working voltage; the detection electrode system comprises a pair of detection electrodes, and analyte test is carried out by applying a direct-current working voltage; the elevated layers include an exhaust elevated layer, a reaction elevated layer, and a detection zone. The invention also discloses a temperature compensation method for the hematocrit test, which comprises a hematocrit test equation with temperature compensation. The invention is beneficial to the electrochemical sensor to obtain accurate detection results in a larger temperature range, has reasonable structure and simple process, and is beneficial to large-scale manufacture.
Description
Technical Field
The invention belongs to the technical field of medical equipment, relates to an electrochemical sensor for detecting an analyte in a blood sample, and particularly relates to an electrochemical sensor with a temperature-compensated red blood cell pressure-volume test function.
Background
Currently, electrochemical sensors are widely used in point of care testing (POCT) and gradually popularized to home users, people can conveniently monitor the content of analytes (such as glucose, uric acid, cholesterol, etc.) in blood samples, whether the detection result is accurate and reliable, and whether the price is low is more and more concerned.
As clearly required in general technical conditions for in vitro diagnostic test systems-blood glucose monitoring systems for self-test (i.e. ISO15197:2013 standard), the measured value difference between each of the hematocrit level and the intermediate hematocrit level (42% + -2%) is not more than 10mg/dl when the glucose concentration is less than 100 mg/dl; at glucose concentrations greater than 100mg/dl, the measured relative difference between each of the hematocrit level and the intermediate hematocrit level (42% ± 2%) is no more than 10%. If whole blood samples containing the same glucose content but having hematocrit values of 20%, 42% and 70% were tested, three different glucose readings would be reported by a system based on a set of calibration constants (e.g., slope and intercept of whole blood samples containing 42% hematocrit values). Even though the glucose concentration is the same, the system will report that a 20% hematocrit whole blood sample contains more glucose than a 42% hematocrit whole blood sample, and that a 70% hematocrit whole blood sample contains less glucose than a 42% hematocrit whole blood sample due to the diffusion of the red blood cells interfering analytes and/or mediators to the electrode surface. Therefore, the concentration of the analyte must be calibrated based on the hematocrit value. In general, an ac working voltage is generally used to test a blood sample, an electrical signal related to the hematocrit is obtained, a hematocrit value of the blood sample to be tested is obtained through a related test equation, and then a calibration equation related to the hematocrit value and the analyte concentration is utilized to finally realize the calibration of the analyte to be tested of the electrochemical sensor.
The electrochemical sensor works on the principle that the concentration of an analyte in a test sample is converted into a corresponding electric signal, for example, when the analyte is glucose in blood, the electrochemical sensor obtains a current signal of the blood sample by applying an operating voltage, and a corresponding blood glucose value can be obtained by a calibration equation. In the electrode reaction process of the electrochemical sensor, reactants firstly diffuse to the surface of the electrode to react, and the transfer speed of the reactants depends on the mass transfer coefficient of the solution. The solute mass transfer coefficient in blood is mainly affected by the hematocrit, the higher the hematocrit value, the smaller the mass transfer coefficient, and vice versa. Typically, negative bias (i.e., lower calculated analyte concentration) occurs at high hematocrit and positive bias (i.e., higher calculated analyte concentration) occurs at low hematocrit. While normal human hematocrit ranges from about 35% to 55%, some humans have hematocrit between about 20% and 70%, and this broad whole blood hematocrit range can result in significant errors in the electrochemical sensor. Therefore, there is a real need for an electrochemical sensor with a hematocrit correction function.
Patent CN104634822a proposes to detect glucose concentration using hematocrit correction. Among these are mentioned the calculation ways of the peak value of the response signal into the hematocrit value, such as: y=ax+b, (Y is the hematocrit value, X is the peak value, and a and b are predetermined coefficients).
Patent CN105021805a proposes a method for correcting physiological parameters of human body. And determining a correction coefficient corresponding to the hematocrit value of the detection sample according to a corresponding relation between the predetermined hematocrit value and the correction coefficient, and correcting the detection concentration of the physiological parameter of the detection sample by using the correction coefficient to obtain a correction concentration, wherein the correction concentration=the correction coefficient is the detection concentration.
Patent CN 106770461A proposes the step of obtaining the hematocrit value of a blood sample: calculating a first median A from the current value obtained during the application time of the third voltage between 0 and 0.5 seconds 1 Calculating a second median A from the current value obtained during the application time of the third voltage between 1 and 2 seconds 2 The hematocrit value is (A) 1 /A 2 )*100。
In order to realize the function of correcting the hematocrit, it is first required to realize an accurate test of the hematocrit. However, unlike a hospital environment, home users are at a relatively wide ambient temperature, such as may reach 10 ℃ in winter and 35 ℃ in summer. The hematocrit test of a blood sample can be greatly affected by the ambient temperature of the electrochemical sensor. Therefore, the accurate hematocrit value can be obtained only by performing corresponding temperature compensation on the hematocrit test of the blood sample at different temperatures, and the accurate measurement of the analyte can be realized by correcting the current value through the hematocrit value.
In addition, the structural design of the electrochemical sensor is also important to realize accurate test of the hematocrit, for example, unsmooth blood injection, pollution of the correction electrode system area by electrolyte and the like can have adverse effects on the detection result.
Disclosure of Invention
Aiming at the problems existing in the prior art, the invention aims to provide an electrochemical sensor with a temperature compensation function for testing the hematocrit, which is beneficial to the electrochemical sensor to obtain accurate detection results in a larger use temperature range, and the electrochemical sensor has reasonable structural design and simple process and is beneficial to large-scale manufacture.
In order to achieve the aim of the invention, the invention adopts the following technical scheme:
an electrochemical sensor with temperature compensated hematocrit test function, the electrochemical sensor comprising a substrate, an electrode layer, a reactant, a spacer layer, and a hydrophilic membrane; wherein, a notch is arranged at the sample inlet end of the substrate; the electrode layer comprises a correction electrode system and a detection electrode system which are positioned on the same plane, the correction electrode system comprises a pair of correction electrodes, and the hematocrit test is carried out by applying alternating current working voltage; the detection electrode system comprises a pair of detection electrodes, and analyte test is carried out by applying a direct-current working voltage; the elevated layer comprises an exhaust elevated layer, a reaction elevated layer and a detection area, wherein the detection area is arranged in the reaction elevated layer and is narrowed from the entrance.
Further, a limiting electrode is arranged between the positive electrode correcting system and the detecting electrode system, and the limiting electrode is a rectangular carbon electrode.
Further, the notch is arc-shaped; the detection area is trapezoidal in shape.
Further, the substrate, the electrode layer, the reactant, the pad layer and the hydrophilic film are sequentially arranged from bottom to top.
Further, the substrate is made of polyethylene terephthalate; the electrode layer is made of carbon; the material of the pad layer is modified polyacrylic acid double faced adhesive tape; the hydrophilic film is made of polyethylene terephthalate.
A temperature compensation method for testing the hematocrit test utilizes the electrochemical sensor to test the hematocrit, and when a blood sample is detected, an alternating current working voltage is provided for a correction electrode system, so that an electric signal related to the hematocrit of the blood sample, namely an AD value, is obtained. Substituting the environmental temperature T and AD value into a hematocrit test equation with temperature compensation, and obtaining an accurate hematocrit value. The specific scheme is as follows:
step 1: at a certain ambient temperature T, respectively testing the AD values of different hematocrit blood samples, taking the hematocrit value as an ordinate and the corresponding AD value as an abscissa, performing polynomial fitting, preferably, performing first-order linear fitting, to obtain a hematocrit test equation y=ax+b at the temperature T (x represents the AD value of the blood sample, y represents the hematocrit value, and a and b are correlation coefficients). By analogy, the hematocrit test equation at different ambient temperatures can be obtained as shown in the following table:
TABLE 1 erythrocyte pressure volume test equation at different ambient temperatures
Step 2: the hematocrit test equation with temperature compensation is established by:
respectively taking each temperature as an abscissa and corresponding to each hematocrit test equation first order term coefficient as an ordinate, performing polynomial fitting, preferably first order linear fitting, to obtain z=a 1 T+B 1 (z represents a coefficient of a first order term, T represents temperature, A 1 And B 1 Is a correlation coefficient);
respectively taking each temperature as an abscissa and corresponding each constant term of the hematocrit test equation as an ordinate, performing polynomial fitting, preferably, performing first-order linear fitting to obtain u=a 2 T+B 2 (u represents a constant term, T represents temperature, A) 2 And B 2 Is a correlation coefficient);
the hematocrit test equation with temperature compensation is y= (a) 1 T+B 1 )x+(A 2 T+B 2 ) (y represents the hematocrit value, T represents the ambient temperature, x represents the AD value, A 1 And B 1 A is a 2 And B 2 Is a correlation coefficient);
step 3: substituting the AD value of the blood sample and the ambient temperature T into the hematocrit test equation with temperature compensation in the step 2 to obtain an accurate hematocrit value.
The invention has the following beneficial effects:
(1) The substrate layer at the sample inlet end of the electrochemical sensor is provided with an arc-shaped notch, and the reaction pad upper layer is provided with a trapezoid detection area with a wide and narrow inlet and outlet, so that the sample injection speed is improved by the design, the sample injection is completed rapidly, and the accurate test value is obtained.
(2) And a limiting electrode is arranged between the positive electrode correcting system and the detecting electrode system, so that electrolyte in a reaction reagent on the detecting electrode system can be effectively prevented from diffusing to the positive electrode correcting system, and the positive electrode correcting system is prevented from being polluted to influence a test value.
(3) Effective separation between the calibration electrode system and the detection electrode system can be respectively and independently tested: calibrating the electrode system to test the hematocrit; the detection electrode system tests various analytes (the analytes can be glucose, uric acid, cholesterol and the like in blood), and when the detection electrode system tests different analytes, the current value of the analytes can be corrected by utilizing the hematocrit value, so that the more accurate analyte concentration can be obtained. The design of the independent test of the electrode system of the invention enhances the application range of the electrochemical sensor.
(4) The electrochemical sensor has reasonable structural design and simple process, and is beneficial to large-scale manufacture.
(5) The invention also provides a temperature compensation method for the hematocrit test, which is favorable for the electrochemical sensor to obtain accurate detection results in a larger use temperature range.
Drawings
FIG. 1 is a schematic structural diagram of an electrochemical sensor according to the present invention: the device comprises a 1-substrate layer, a 11-notch, a 2-electrode layer, a 21-first correction electrode, a 22-second correction electrode, a 23-limiting electrode, a 24-first detection electrode, a 25-second detection electrode, a 3-reagent layer, a 4-heightening layer, a 41-exhaust heightening layer, a 42-reaction heightening layer, a 43-detection area, a 5-hydrophilic membrane layer and a 6-electrochemical sensor, wherein the substrate layer is arranged on the substrate layer;
FIG. 2 is a graph showing the absolute deviation of hematocrit values with or without temperature compensation at an ambient temperature of 10 ℃;
FIG. 3 is a graph showing the comparison of absolute deviation of hematocrit values with or without temperature compensation at an ambient temperature of 39 ℃.
Detailed Description
The following detailed description of the present invention is given by way of specific examples, which are given for illustrative purposes only and are not to be construed as limiting the scope of the present invention.
As shown in fig. 1, the structure of the electrochemical sensor with temperature compensated hematocrit test function: the electrode comprises a substrate layer 1, an electrode layer 2, a reagent layer 3, a pad layer 4 and a hydrophilic film layer 5 from bottom to top in sequence; the sample inlet end of the substrate layer 1 is provided with a notch 11, which is arc-shaped in the embodiment. The electrode layer 2 comprises a correction electrode system and a detection electrode system, the correction electrode system and the detection electrode system are positioned on the same plane, the correction electrode system comprises a first correction electrode 21 and a second correction electrode 22, and the hematocrit test is carried out by applying alternating working voltage; the detection electrode system comprises a first detection electrode 24 and a second detection electrode 25, and analyte testing is performed by applying a dc operating voltage. The detection electrode system is covered with a reagent layer 3. A limiting electrode 23 is arranged between the calibration electrode system and the detection electrode system, and the limiting electrode 23 in the embodiment is a rectangular carbon electrode. The elevated layer 4 includes an exhaust elevated layer 41, a reaction elevated layer 42, and a detection region 43, the detection region 43 is provided in the reaction elevated layer 42, the detection region 43 is provided from an entrance to be narrowed, and preferably, the detection region 43 is trapezoidal in shape. A hydrophilic film layer 5 is covered on the backing layer 4.
Preferably, the substrate layer 1 is made of polyethylene terephthalate; the electrode layer 2 is made of carbon; the material of the pad layer 4 is modified polyacrylic acid double faced adhesive tape, and the thickness is 0.125um; the hydrophilic film layer 5 is made of polyethylene terephthalate, and the hydrophilic film layer 5 is subjected to single-sided hydrophilic treatment.
The manufacturing process of the glucose electrochemical sensor of the embodiment is as follows:
the liquid reagent is prepared first, and then the reagent is dispensed to the detection area 43 by dispensing (the load of each electrochemical sensor is 0.7-1.2 uL). Then heat-treating for 10min in the drying tunnel section at 30-40 ℃, the drying tunnel section at 40-50 ℃ and the drying tunnel section at 50-60 ℃ in sequence. And (3) attaching double faced adhesive tape, hydrophilic film, cutting, and storing the glucose electrochemical sensor in a sealed plastic cylinder with molecular sieve drying agent. The minimum sample size that can be tested for a glucose electrochemical sensor is 0.6uL.
The experimental procedure for performing the hematocrit test using the electrochemical sensor of this example was as follows:
first, venous whole blood samples having a total of 6 concentration gradients of 20%,30%,42%,50%,60% and 70% in hematocrit value were prepared, respectively. Then, glucose sensors at 5℃and 10℃and 17℃and 23℃and 32℃and 39℃and 45℃were used to test the 6 concentration gradient venous whole blood samples in sequence. During detection, 100hz and 500mv of alternating current working voltage is applied to the correction electrode system, and an electric signal related to the hematocrit, namely an AD value, is obtained. To facilitate data processing, the AD value is divided by 100000, labeled test AD value. The test was repeated 5 times under each test condition, and the average value of the test AD values was calculated as shown in tables 2 to 8.
TABLE 2 data for the hematocrit test at 5℃
TABLE 3 data for the hematocrit test at 10℃
Table 4 data from the hematocrit test at 17℃
Table 5 data from the hematocrit test at 23℃
TABLE 6 data for the hematocrit test at 32℃
TABLE 7 data for the hematocrit test at 39℃
Table 8 data for the hematocrit test at 45℃
It can be seen from tables 2-8 that the AD values are more reproducible.
The experimental data in tables 2-8 were processed:
(1) The average value of the AD values measured at 5, 10, 17, 23, 32, 39, and 45℃is taken as the abscissa, and the corresponding hematocrit values 20%,30%,42%,50%,60%, and 70% are taken as the ordinate, and linear fitting is performed according to the least squares method to obtain 7 sets of first-order hematocrit test equations (i.e., hematocrit test equations at different ambient temperatures without temperature compensation) as shown in Table 9.
(2) Performing linear fitting to obtain z=a by taking 5 ℃,10 ℃,17 ℃,23 ℃, 32 ℃,39 ℃ and 45 ℃ as abscissa and taking the first term coefficient of the hematocrit test equation at each temperature as ordinate 1 T+B 1 Wherein z represents a coefficient of a primary term, T represents temperature, A 1 And B 1 Is a correlation coefficient.
(3) Performing a first linear fit with the constant term of the hematocrit test equation at each temperature as the ordinate, taking 5 ℃,10 ℃,17 ℃,23 ℃, 32 ℃,39 ℃ and 45 ℃ as the abscissa, to obtain u=a 2 T+B 2 Wherein u represents a constant term, T represents temperature, A 2 And B 2 Is a correlation coefficient.
(4) The hematocrit test equation with temperature compensation is: y= (a 1 T+B 1 )x+(A 2 T+B 2 ) Wherein y represents the hematocrit value, T represents the ambient temperature, x represents the AD value, A 1 And B 1 A is a 2 And B 2 Is a correlation coefficient.
Substituting the AD value of the blood sample and the ambient temperature T into y= (a) 1 T+B 1 )x+(A 2 T+B 2 ) The accurate hematocrit value can be obtained.
TABLE 9 Equipped test equation for hematocrit at different ambient temperatures
| Ambient temperature (. Degree. C.) | Erythrocyte pressure volume test equation | Coefficient of primary term | Constant term | R 2 |
| 5 | y＝-1.5698x+1.1291 | -1.5698 | 1.1291 | 0.9987 |
| 10 | y＝-1.6449x+1.1767 | -1.6449 | 1.1767 | 0.9994 |
| 17 | y＝-1.431x+1.1391 | -1.4310 | 1.1391 | 0.9965 |
| 23 | y＝-1.2985x+1.1041 | -1.2985 | 1.1041 | 0.9989 |
| 32 | y＝-1.2112x+1.1044 | -1.2112 | 1.1044 | 0.9979 |
| 39 | y＝-1.1087x+1.0774 | -1.1087 | 1.0774 | 0.9830 |
| 45 | y＝-1.0197x+1.0434 | -1.0197 | 1.0434 | 0.9982 |
It can be seen from table 9 that the hematocrit test equation has a better linearity at different ambient temperatures.
Next, using the hematocrit test equations of table 9 under different ambient temperatures, using each temperature as an abscissa, and using the coefficient of the first term corresponding to each hematocrit test equation as an ordinate, performing a first linear fit to obtain equation (1):
z＝0.0153T-1.6996 (1)
wherein z represents a coefficient of a primary term, T represents temperature, R 2 ＝0.9538。
Then, using the hematocrit test equations of table 9 under different ambient temperatures, respectively taking each temperature as an abscissa, and taking the constant term coefficient corresponding to each hematocrit test equation as an ordinate, performing a first-time linear fitting to obtain equation (2):
u＝-0.0026T+1.1733 (2)
wherein u represents a constant term coefficient, T represents temperature, R 2 ＝0.7843。
And obtaining a red blood cell pressure volume test equation with temperature compensation according to the equations (1) and (2), namely an equation (3):
y＝(0.0153T-1.6996)x+(-0.0026T+1.1733) (3)
wherein y represents the hematocrit, T represents the temperature, and x represents the AD value.
The test AD values and temperature data of tables 2-8 were substituted into equation (3) to obtain the test hematocrit values of tables 10-16, and the average value and absolute deviation of the five tests were calculated, where absolute deviation = average value-hematocrit value.
Table 10 test hematocrit values at 5℃
Table 11 test hematocrit values at 10℃
Table 12 test hematocrit value at 17 deg.c
TABLE 13 measurement of hematocrit values at 23℃
Table 14 test hematocrit value at 32 deg.c
TABLE 15 test hematocrit value at 39℃
Table 16 test hematocrit value at 45℃
From the test hematocrit values of tables 10-16, it can be seen that the error of the hematocrit value measured within ±5% in the range of 5 ℃ to 45 ℃ is higher in accuracy by using the hematocrit test equation with temperature compensation, equation (3), which indicates that the electrochemical sensor of the present invention can obtain accurate detection results in a larger use temperature range.
Comparative test (with or without temperature compensation):
(1) The temperature-compensated test hematocrit values were calculated at 10 ℃ (test AD values see table 3) and 39 ℃ (test AD values see table 7) using the hematocrit test equation y= -1.2985x+1.1041 at 23 ℃ in table 9 (typically, fitted hematocrit equations at room temperature (23 ℃ ±2 ℃) were used for testing, so that the deviation was large at low temperatures such as 10 ℃ and high temperatures such as 39 ℃ and experimental data were significant), and the average and absolute deviation of the five tests were calculated, wherein absolute deviation = average value-hematocrit value, and the results are shown in tables 17 and 18.
Table 17 test hematocrit value at 10℃
Table 18 test hematocrit value at 39 c
(2) Using the temperature compensated hematocrit test equation y = (0.0153T-1.6996) x + (-0.0026t+1.1733) (i.e., equation (3)), temperature compensated test hematocrit values were calculated for ambient temperatures of 10 ℃ and 39 ℃ respectively, and absolute deviations were calculated.
(3) As shown in fig. 2 and 3, it can be seen that the packed red blood cell volume values after temperature compensation are more accurate in the environments of 10 ℃ and 39 ℃.
Claims (5)
1. A temperature compensation method for a hematocrit test is characterized in that,
performing a hematocrit test using the electrochemical sensor, the calibration electrode system providing an alternating operating voltage, thereby obtaining an electrical signal related to the hematocrit of the blood sample, i.e., an AD value; establishing a hematocrit test equation with temperature compensation, substituting the environmental temperature T and AD value into the hematocrit test equation with temperature compensation, and obtaining an accurate hematocrit value;
the hematocrit test equation with temperature compensation is established by:
(1) Respectively testing AD values of different hematocrit blood samples at a certain ambient temperature T, performing polynomial fitting by taking the hematocrit value as an ordinate and the corresponding AD value as an abscissa to obtain a hematocrit test equation y=ax+b at the ambient temperature T, wherein x represents the AD value, y represents the hematocrit value, a and b are correlation coefficients, and so on, so that the hematocrit test equation at different ambient temperatures can be obtained;
(2) Respectively taking each temperature as an abscissa and a first order coefficient corresponding to each hematocrit test equation as an ordinate, and performing polynomial fitting to obtain z=a 1 T+B 1 Wherein z represents a coefficient of a primary term, T represents temperature, A 1 And B 1 Is a correlation coefficient;
(3) Respectively taking each temperature as an abscissa and a constant term corresponding to each hematocrit test equation as an ordinate, and performing polynomial fitting to obtain u=a 2 T+B 2 Wherein u represents a constant term, T represents temperature, A 2 And B 2 Is a correlation coefficient;
(4) The hematocrit test equation with temperature compensation was derived: y= (a 1 T+B 1 )x+(A 2 T+B 2 ) Wherein y represents the hematocrit value, T represents the ambient temperature, x represents the AD value, A 1 And B 1 A is a 2 And B 2 Is a correlation coefficient;
wherein the electrochemical sensor comprises a substrate, an electrode layer, a reaction reagent, a pad layer and a hydrophilic film; wherein, a notch is arranged at the sample inlet end of the substrate; the electrode layer comprises a correction electrode system and a detection electrode system which are positioned on the same plane, the correction electrode system comprises a pair of correction electrodes, and the hematocrit test is carried out by applying alternating current working voltage; the detection electrode system comprises a pair of detection electrodes, and analyte test is carried out by applying a direct-current working voltage; the heightening layer comprises an exhaust heightening layer, a reaction heightening layer and a detection area, wherein the detection area is arranged in the reaction heightening layer and is narrowed from an inlet; and a limiting electrode is arranged between the correction electrode system and the detection electrode system, and the limiting electrode is a rectangular carbon electrode.
2. The temperature compensation method of claim 1, wherein the notch is arc-shaped in shape; the detection area is trapezoidal in shape.
3. The temperature compensation method according to claim 1 or 2, wherein the substrate, the electrode layer, the reactant, the spacer layer and the hydrophilic film are disposed in this order from bottom to top.
4. The temperature compensation method according to claim 1 or 2, wherein the substrate is made of polyethylene terephthalate; the electrode layer is made of carbon; the material of the pad layer is modified polyacrylic acid double faced adhesive tape; the hydrophilic film is made of polyethylene terephthalate.
5. The temperature compensation method of claim 1 wherein the polynomial fit is a first order linear fit.
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| CN108982501A (en) * | 2018-07-25 | 2018-12-11 | 赖海燕 | A kind of medical treatment blood detector equipment and system |
| CN108896635A (en) * | 2018-09-20 | 2018-11-27 | 江苏鱼跃医疗设备股份有限公司 | A kind of beta-hydroxybutyric acid electrochemical sensor |
| CN109341899B (en) * | 2018-09-21 | 2021-02-09 | 深圳市国赛生物技术有限公司 | Temperature correction method, device and computer readable storage medium |
| CN109884150B (en) * | 2019-03-08 | 2021-05-14 | 武汉璟泓科技股份有限公司 | Erythrocyte backlog correction method and storage medium |
| CN111239228A (en) * | 2020-02-24 | 2020-06-05 | 江苏鱼跃医疗设备股份有限公司 | Electrochemical biosensor and method for measuring blood impedance phase angle |
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